JPH1156772A - Optical tomograph - Google Patents

Abstract

PROBLEM TO BE SOLVED: To improve endoscope maneuverability such as automatically imaging a tomographic image part of the part, which is corresponding to an area under observation by the endoscope. SOLUTION: This device leads low-coherent light mixed with guide-light into a forceps-channel 17 of an endoscope 2. An optical-scanning probe 9, which irradiates to the peripheral direction, is inserted from the tip the device. The image taken by an imaging means installed to the tip of an inserted part 16 is displayed on a monitor 7, as an endoscopic image 27, by a frame memory 6 for usual images. And, the device detects the beaming direction of the guide- light by detecting frames in which the guide-light is showing up in a prescribed area of the endoscopic image 27, and controls automatic display of laminagraphic images of the part corresponding to the area displayed as the endoscopic images 27.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

The present invention relates to an optical tomographic imaging apparatus for obtaining an optical tomographic image of a subject using low interference light.

[0002]

2. Description of the Related Art In recent years, when diagnosing a living tissue, in addition to an image display device such as an endoscope device which obtains optical information on the surface state of the tissue, a light capable of obtaining optical information inside the tissue. A CT device has been proposed.

The optical CT apparatus uses picosecond pulses to detect information inside a living body and obtain a tomographic image. However, laser light sources that generate extremely short pulse light on the order of picosecond pulses are expensive, large, and cumbersome to handle.

[0004] Recently, an interference type OCT (optical optical system) for obtaining a tomographic image of a subject using low coherence light has been proposed.
Coherence tomography) is disclosed in, for example,
No. 1312 is disclosed. In this conventional example, when observing a body cavity in the digestive tract or the like, a tomographic image is obtained by inserting an OCT probe into a channel of an endoscope and scanning light in a circumferential direction.

[0005]

In a large lumen such as the stomach, when used together with an endoscopic observation image, the correspondence between the part observed endoscopically and the tomographic image scanned in the circumferential direction is used. In order to obtain information that makes the relationship unclear and easy to diagnose, it is necessary to perform an operation of extracting a tomographic image part corresponding to the part observed endoscopically and displaying only that part. Indeed, the operation was troublesome.

SUMMARY OF THE INVENTION The present invention has been made in view of the above points, and has good operability such as automatically displaying a tomographic image portion corresponding to a region observed by an endoscope. It is intended to provide a device.

[0007]

An illumination means for emitting illumination light for illuminating a specific portion of the subject, an objective optical system for forming an image of the specific portion of the subject illuminated with the illumination light, and A solid-state imaging device that captures an image of the subject, an elongated insertion portion that can be inserted into the subject, a light source that generates low-interference light, A light guide means comprising one single mode fiber for emitting the low interference light to the sample and detecting the reflected light reflected from the subject, and a light emitted from the single mode fiber to a distal end of the insertion section. In order to further scan and output the light in the circumferential direction, the driving means for rotating the single mode fiber interferes with the reference light generated from the light source and reflected from the subject detected by the single mode fiber. An interference light extraction unit that extracts an interference signal corresponding to the interfered interference light, and a signal processing unit that performs signal processing corresponding to the interference signal and constructs a tomographic image of the subject in a depth direction. In the optical tomographic imaging apparatus provided, the light emitted from the distal end of the insertion portion, the light irradiated to the subject is captured by the solid-state imaging device, and the direction of the light emitted from the distal end of the insertion portion is detected from the image, By providing a control circuit for controlling the region or the direction in which the tomographic image is displayed from the direction, it is possible to set to display a tomographic image in a region corresponding to the region of the image captured by the solid-state imaging device, and to improve operability. Can be improved.

[0008]

Embodiments of the present invention will be described below with reference to the drawings. (First Embodiment) FIGS. 1 to 3 relate to a first embodiment of the present invention, and FIG. 1 shows an entire configuration of an optical tomographic imaging apparatus according to the first embodiment of the present invention. 2 shows a configuration of the OCT processor, and FIG. 3 shows an endoscope image.

An optical tomographic imaging apparatus 1 according to a first embodiment of the present invention shown in FIG. 1 includes an endoscope 2 having built-in image pickup means, and a light guide 3 of the endoscope 2 which emits illumination light in a visible region. A light source device 4 for supplying, a CCU 5 for performing signal processing for generating an image in a visible region with respect to an output signal of the imaging means,
The endoscope image generated in U5 is stored in the frame memory 6 for normal image.
A OCT processor 8 that performs processing for generating a low-interference image using low-interference light,
The base end is connected to the OCT processor 8 and the endoscope 2
An optical scanning probe 9 that penetrates a forceps channel 17 provided in an insertion portion 16 of the optical scanning probe 9 and scans low-interference light in a circumferential direction;
A laser light source 11 for supplying a laser beam serving as a guide light having a wavelength in the visible region (for example, a wavelength of 630 nm) to the processor 8, an OCT image frame memory 12 for storing an OCT image output from the OCT processor 8, and A color extraction circuit 13 for extracting guide light from the image data in the image frame memory 6, and an OCT
And a control circuit 14 that controls to select an OCT image portion of an area corresponding to the endoscope image from the image frame memory 12 and display the selected OCT image portion on the monitor 7.

The endoscope 2 has an elongated and flexible insertion portion 16, and a forceps channel 17 is provided in the insertion portion 16, and the optical scanning probe 9 is inserted through the insertion opening of the forceps channel 17.
And the distal end of the optical scanning probe 9 can be projected from the distal end opening of the forceps channel 17.

By connecting the proximal end of the light guide 3 inserted through the insertion portion 16 to the light source device 4, the white light of the lamp 18 is guided by the light guide 3, and the distal end of the insertion portion 16. The distal end surface fixed to the illumination window of the unit 19 is further radiated to the subject 22 through the illumination lens 21.

The light reflected on the surface of the subject 22 forms an image at an image forming position by an objective lens 23 attached to an observation window adjacent to the illumination window. At this image forming position, CCD2
4 are arranged.

In order to maintain color reproducibility, an infrared cut filter 25 is arranged in front of the imaging surface of the CCD 24, and a mosaic filter for optically separating colors to perform color imaging under white light. 26 are arranged.

The signal picked up by the CCD 24 and photoelectrically converted is input to the CCU 5, subjected to signal processing, converted into a digital video signal, and converted into a digital video signal (corresponding to a normal endoscope image under white illumination). The image is temporarily stored in the image frame memory 6. Then, a normal endoscope image 27 is displayed on the monitor 7 via a D / A converter (not shown).

On the other hand, as shown in FIG. 2, the OCT processor 8 has a super-bright light emitting diode (hereinafter, referred to as a low interference light source) as a low interference light source.
SLD). The SLD 31 has the characteristic of low coherence light that exhibits coherence only in a short distance range such that its wavelength is in the infrared region of, for example, 1300 nm and its coherent distance is, for example, about 17 μm. This SL
The light of D31 enters one end of the first single mode fiber 32 and is transmitted to the other end surface (tip surface).

The first single mode fiber 32 is optically coupled to a second single mode fiber 34 at an optical coupler 33 in the middle. Therefore, the light is branched and transmitted by the optical coupler unit 33.

A rotary joint 3 is provided at the distal end of the first single mode fiber 32 (from the coupler 33).
5 is inserted into the optical scanning probe 9 through the rotary joint 35, and the SLD 3 is inserted into one end (base end) of a third single mode fiber 36 which is driven to rotate.
One light is incident, and is guided by the third single mode fiber 36 to the other end (front end).

The second single mode fiber 34
The laser light source 11 that emits light at a specific wavelength in the visible wavelength range via a dichroic mirror 37 is disposed at one end of the laser light source. The dichroic mirror 37 has a characteristic of selectively reflecting light of the wavelength of the SLD 31 and transmitting visible laser light serving as guide light.

Therefore, the laser light is transmitted through the dichroic mirror 37 and is incident on one end of the second single mode fiber 34. Therefore, the third single mode fiber 3 that is inserted into the optical scanning probe 9 and is driven to rotate.
6 guides not only the light of the SLD 31 but also the laser light combined with this light.

The motor 4 is provided in the outer tube of the optical scanning probe 9.
The gear attached to the rotating shaft of the motor 41 meshes with the gear 42 attached to the third single mode fiber 36, and the third single mode fiber 36 rotates with the rotation of the motor 41. A prism 43 for changing the optical path is attached to the distal end of the third single mode fiber 36 via a fixing member, and the light emitted from the distal end face of the third single mode fiber 36 is formed at a right angle by the slope of the prism 43. And emits light radially in a direction perpendicular to the axis of the optical scanning probe 9.

The second single mode fiber 34
A lens 44 and a mirror 45 are arranged opposite to the other end of the mirror 45. The mirror 45 can change the optical path length by an actuator 46 as shown by an arrow. Further, the second single mode fiber 34 is provided with a loop portion 47 on the other end side from the optical coupler portion 33. In addition,
The actuator 46 and the motor 41 are controlled by the control device 48.

The loop portion 47 is set, for example, to have a length substantially equal to the length of the third single mode fiber 36, and is reflected by the mirror 45 from the distal end surface of the second single mode fiber 34 to form the second single mode fiber 34. The optical path length returning to the distal end face of the mode fiber 34 is radiated from the distal end face of the third single mode fiber 36 to the subject 22 side via the prism 43, is reflected inside the vicinity of the surface of the subject 22, and becomes the third optical path length. The length of the optical path returning to the end face of the single mode fiber 36 can be made equal.

By shifting the position of the mirror 45 in the direction of the arrow via the actuator 46, the optical path length on the reference light side (reference light side) is changed, and the optical path on the measurement light side that interferes with this is changed. The length (more specifically, the optical path length in the depth direction of the subject 22) can be changed.

The second single mode fiber 34
A photodetector 51 for receiving light reflected by the dichroic mirror 37 is disposed at one end of the photodetector 51. The light photoelectrically converted by the photodetector 51 is amplified by an amplifier 52,
The signal is input to the demodulator 53.

The demodulator 53 performs a demodulation process for extracting only the signal portion of the interfering interference light, and its output is converted into a digital signal via an A / D converter 54 and input to a computer 55.

The computer 55 controls the rotation of the motor 41 via the control device 48 to control the radial scanning of the low-interference light, and controls the movement of the mirror 45 by the actuator 46 so that the depth of the subject 22 can be controlled. By controlling the scanning in the vertical direction, image data of a tomographic image is generated and temporarily stored in the OCT image frame memory 12.

In this case, for example, the computer 55 controls the mirror 45 by the actuator 46 via the control device 48.
Is moved in the depth direction of the subject 22, the motor 41 is further rotated, and the low-interference light is radially scanned by scanning, so that a tomographic image corresponding to one frame in the circumferential direction with respect to the subject 22 is obtained. An image (OCT image) can be obtained. Since the reciprocation of the actuator 46 is very fast with respect to the radial scanning speed of the low interference light, a sufficient resolution in the circumferential direction can be obtained. The OCT image data is stored in the OCT image frame memory 12.

The OCT image data stored in the OCT image frame memory 12 is read out from the normal image frame memory 6 by the control circuit 14 and the OCT image data corresponding to the area of the endoscope image 27 displayed on the monitor 7. It is controlled so that only the image data portion is read, and the monitor 7
The CT image 56 is displayed.

In order to specify the OCT image data portion corresponding to the area of the endoscope image 27 by the control circuit 14,
The normal image data of the normal image frame memory 6 is input to the color extraction circuit 13, and there is a laser light serving as a guide light mixed with the circumferentially scanning light of the low interference light from the tip side of the optical scanning probe 9. The frame of the normal image to be detected is detected.

The detection data is sent to the control circuit 14,
The control circuit 14 reads the OCT image frame memory so as to read out the OCT image data portion corresponding to the area of the endoscope image 27 from the frame at the timing when the detection data is obtained (for the scanning of the low interference light in the circumferential direction). Twelve read addresses are controlled. Then, the endoscope image 27 is displayed on the monitor 7.
And the OCT image 56 in the area corresponding to the endoscope image 27 is automatically displayed.

First, the operation of obtaining an OCT image will be briefly described. The optical scanning probe 9 scans the low-interference light in the circumferential direction, and in the return light from the subject 22 in each scanning direction, only light whose optical path length almost coincides with the reference light side interferes. The signal is extracted by the demodulator 53 via the photodetector 51 and the like, and is stored in the memory cell designated by the address appropriately set in the OCT image frame memory 12 via the computer 55. Then, for example, while the mirror 45 is moved at high speed via the actuator 46, one rotation scan is performed in the circumferential direction, so that tomographic image data can be obtained.

Since the relative relationship with the endoscope image 27 obtained via the solid-state imaging device (specifically, the CCD 24) is unclear as it is, the area of the endoscope image 27 is set as follows. OCT image 5 of corresponding part or area
6 is displayed. Next, an endoscope image 27 and an OCT image 56 of an area corresponding to the endoscope image 27 are displayed on the monitor 7.
Will be described.

First, the optical scanning probe 9 is passed through the forceps channel 17 of the endoscope 2 and the distal end thereof is moved to the forceps channel 1.
7 is made to protrude from the opening at the tip of the endoscope 7 for endoscopic observation. That is, the white light of the lamp 18 of the light source device 4 is
Then, from the distal end side, the circumferential direction of the distal end portion 19 is set and illuminated on the inspection part side of the subject 22 to be observed in the subject 22. The reflected light from the illuminated inspection site and the tip of the probe causes the CCD 2 to pass through the objective lens 23.
An optical image (visible optical image) of the inspection site and the tip of the probe is formed on the imaging surface of No. 4 and photoelectrically converted.

The photoelectrically converted signal is subjected to signal processing by the CCU 5, converted into a color video signal, digitized, and stored in the R, G, B frame memories constituting the normal image frame memory 6, for example, every 1/30 seconds. Is stored. This R,
The endoscope image data stored in the G and B frame memories is 1
1/3 so that a probe image 9 'on the distal end side of the optical scanning probe 9 on the endoscope image 27 can be observed, for example, near the center as shown in FIG. 1 or FIG. Become.

Next, a control signal is sent from the computer 55 of the OCT processor 8 to the control device 48 so as to start generating a one-frame tomographic image. In response to this, the control device 48 rotates the motor 41 at a constant speed. By the rotation of the motor 41, the third single mode fiber 36 rotates at a speed of, for example, 4 to 6 rotations / sec.

The motor 41 (or the rotary joint 3)
Reference position detection means (not shown) (for example, a rotary encoder may be used, or a photo interrupter or the like may be used) is attached to each of the five portions. The rotational position of the third single mode fiber 36 is set in advance. A trigger signal serving as a reference position detection signal is generated at the timing of passing the reference position, and sent to the control circuit 14 via the control device 48, for example, to start an operation for automatically setting the OCT image display area.

The control circuit 14 detects the guide light, that is, the visible laser light in a certain area on the endoscope image 27 by the color extraction by the color extraction circuit 13 from the timing when the trigger signal is generated, or the frame of the frame where the detection is not detected. Perform detection.

More specifically, the control circuit 14 sets the endoscope image 27 at the time of generation of the trigger signal as a reference frame. Then, for example, as shown in FIG.
The number of the frame in which the color of the guide light is first detected in the area a with respect to the longitudinal direction of the probe image 9 ′ as an axis is measured from the reference frame. The timing at which the light is emitted (emission angle or scanning angle) is evaluated (approximately). Next, the number of the frame in which the color of the laser beam from which the laser beam is no longer detected from the region b is measured as compared with the reference frame, and the timing of the emission angle at this time is roughly estimated. The control circuit 14 calculates the timing of the emission angle at which light is emitted in the direction of the visual field of the endoscope image 27 from these two estimates.

Then, address information for reading out the OCT image data portion stored in the OCT image frame memory 12 is calculated and set based on the exit angle, and the OCT image is calculated based on the address information.
OC only in the area specified from the image frame memory 12
The T image data portion is read and sent to the monitor 7. Monitor 7
Simultaneously displays the endoscope image 27 and the OCT image 56 at a portion corresponding to the region displayed as the endoscope image 27 (for example, a cross section along a certain direction in the region).
It is also possible to display only one of them.

This embodiment has the following effects. Since only the tomographic image portion of the area observed by the endoscope 2 can be automatically displayed, the operator does not need to perform the setting, and
Operability is improved. In addition, the endoscope image 2 in the same area
7 and the OCT image 56 can be displayed simultaneously, so that an environment suitable for diagnosis can be provided to the operator.

FIG. 4 shows an optical tomographic imaging apparatus 1 'according to a modification of the first embodiment. In this modification, in FIG.
Instead of the direct-view type endoscope 2, a side-view type endoscope 2 'is employed. The side-view type endoscope 2 'is provided with an optical system for illuminating and observing the side.

A prism 58 is arranged to face the front end surface of the light guide 3, and the illumination light emitted from this front end surface is reflected by the prism 58, and passes through the illumination lens 21 attached to the illumination window opened to the side. The light is emitted to the side of the subject 22. The CCD 24 is located at the image forming position of the objective lens 23 attached to the observation window which is adjacent to the illumination window and opened to the side.
Is arranged.

A mouse 59 is connected to the control circuit 14 as a pointing device.
In step 6, an area to be displayed is specified, and the OCT image 56 of the specified area can be displayed.

Further, by designating a frame at a timing at which the guide light scans in the direction of the visual field on the endoscope image 27 to the control circuit 14, the control circuit 14 transmits the OCT image frame memory 12 at the timing of the designated frame. Is detected, and an OCT image in an area centered on the address can be displayed.

When the OCT image in that area is different from the observation area of the endoscope image 27, the mouse 59
On the displayed OCT image, the cursor can be moved to the area to be displayed and the OCT image in the area in the moving direction can be displayed.

Therefore, even if there is some error in the operation of specifying the frame at the timing when the guide light scans the direction of the field of view first on the endoscope image 27, the frame is corrected to correspond to the endoscope image 27. The OCT image of the area can be displayed.

The other structure is the same as that of the first embodiment. In this modification, the distal end side of the optical scanning probe 9 cannot be captured in the field of view (cannot be displayed) at the center of the endoscope image 27. Therefore, the control circuit 14 is slightly different from that described in the first embodiment. The OCT image 56 of the portion corresponding to the endoscope image 27 is automatically displayed by the modified method.

In this case, first, the viewing direction of the endoscope 2 'is set to the direction to be observed. Then, the automatic setting of the OCT image display area is performed. The control circuit 14 uses the frame of the timing of the generation of the trigger signal as a reference, and determines the number of frames on which the irradiation of the guide light is observed at the center position (in the scanning direction of the guide light) on the endoscope image 27 from the reference frame. Eyes are detected (via the color extraction circuit 13), and the center value of the address when the frame is stored in the OCT image frame memory 12 is calculated.

That is, in this modification, the color extraction circuit 13 performs color extraction to determine whether or not the guide light is detected at the center of the endoscope image 27, and sends a detection signal to the control circuit 14 at the detected timing. Then, the control circuit 14 grasps the frame at the detected timing or specifies the address at that timing.

Then, an address from which the area is read is set appropriately with the address as the center, and the OCT image data of the corresponding area is read from the OCT image frame memory 12 and displayed on the monitor 7. The appropriate area is the mouse 59
Can be set freely.

According to this modified example, the side-view type endoscope 2 '
Therefore, the positional relationship between the endoscope image 27 and the OCT image 56 can be more easily grasped. For example, as shown in FIG. 4, when the imaging unit is set to a part of the subject 22 to be observed, low-interference light radially scans the right part of the part, and a tomographic image (FIG. 4 is displayed on the monitor 7 as an OCT image 56. Then, by moving the insertion section 16 so as to move the distal end portion 19 slightly forward or rearward, a tomographic image of the front side or the rear side in the endoscope image 27 can be obtained (the probe 9 side is the front side or the rear side). You may move to the rear).

Further, according to this modification, the operator can specify the display area of the OCT image, so that it is easier to use. It may be applied to the first embodiment. The other effects are the same as those of the first embodiment.

(Second Embodiment) Next, a second embodiment of the present invention will be described with reference to FIG. In the present embodiment, a laser light source 61 for treatment is provided, an area to be irradiated with the laser light from the laser light source 61 for treatment is designated on the OCT image, and the laser light from the laser light source 61 for treatment is irradiated to the area. I can do it.

The OCT processor 6 according to the present embodiment
2 is shown in FIG. The OCT processor 62 has the same configuration as the OCT processor 8 of FIG. 2 except for the following points. In addition, the same reference numerals are given to the same components, and the description thereof will be omitted.

That is, the laser light from the therapeutic laser light source 61 is transmitted through the dichroic mirror 3 that transmits this laser light.
7 and is incident on one end of the second single mode fiber 34.

The image is processed by the computer 55,
By operating the mouse 59 on the OCT image 56 displayed on the monitor 7 via the OCT image frame memory 12, the cursor 63 can be moved and an arbitrary point can be designated. And cursor 6
3, the start point P1 and the end point P2 of the irradiation area of the laser beam from the therapeutic laser light source 61 can be designated.

Therefore, when a tumor or the like is present in the subject and the treatment is performed by irradiating the tumor portion with a therapeutic laser beam, the starting point P1 is located at the end of the region where the tumor portion exists.
And the end point P2.

For example, when the start point P1 is first designated by the cursor 63, the coordinate position is inputted to the direction detecting section 64, and the reference position P corresponding to a predetermined direction around the reference point K is obtained.
, The direction corresponding to the position of the start point P1 is detected. Similarly, for example, the end point P
Position 2 can also be specified.

The direction information of these points P1 and P2 is input to the laser control unit 65, and the laser control unit 65 uses the optical scanning probe 9 to irradiate the treatment laser light source 61 with light in the direction of the point P1. The laser beam irradiation is started, and control is performed to stop the irradiation of the laser beam from the treatment laser light source 61 at the timing when the light is irradiated in the direction of the point P2.

The irradiation (start) timing is such that the direction in which the third single mode fiber 36 and the like in the optical scanning probe 9 are rotated and the treatment laser light is emitted is from the direction of the reference position to the position of the start point P1. This is done by measuring the time to reach the direction. Similarly, the irradiation is stopped by measuring the time from the direction of the reference position to the direction of the end point P2.

According to the present embodiment, the range of the therapeutic effect can be confirmed on the OCT image 56 at the same time when the therapeutic treatment is performed by the therapeutic laser. Note that O in FIG.
The endoscope 2 shown in FIG. 1 or FIG.
The optical tomographic imaging apparatus may be configured in combination with 2 ′ or the like. In this case, by arranging the guide light generating means facing the dichroic mirror 37, the main function of the first embodiment or its modification can be realized.
Even if the output of the treatment laser light source 61 can be made sufficiently small, without using the guide light generating means,
The OCT image 56 of the portion corresponding to the observation region of the endoscope image 27 can be automatically displayed by the laser light whose output is reduced.

Next, an optical tomographic imaging apparatus capable of observing an affected part or the like observed with an endoscope as a tomographic image from a plurality of directions will be described with reference to FIGS.

As shown in FIG. 6, this optical tomographic imaging apparatus has an overtube 7 through which an insertion portion 73 of an endoscope 72 can be inserted.
4 is formed of a substantially cylindrical tube, and a number of single mode fibers 75 are embedded in the overtube 74.

The base end of each single mode fiber 75 is connected to a single mode fiber 78 connected to an OCT processor 77 via a switching section 76.

The distal end side of each single mode fiber 75 has a structure as shown in FIG. 7 and FIG. That is, a lens 79 is attached to the tip of each single mode fiber 75, and the light is condensed by the lens 79 and guided to the prism 81 arranged in front thereof,
Reflected by the prism 81, the overtube 74
Is emitted to the center side of the.

The insertion portion 73 of the endoscope 72 inserted into the overtube 74 is set such that the distal end surface 82 is at a position retracted slightly behind the distal end surface of the overtube 74.

Therefore, the endoscope 72 is connected to the overtube 74.
The illumination optical system (the light guide 3 and the illumination lens 21) and the observation optical system (the objective lens 23 and the
D24 etc.), the target tissue portion 83 such as the affected part can be observed.

Further, in this state, when a suction operation is performed by the suction pipe 84 provided on the endoscope 72, the target tissue portion 83 is suction-moved toward the distal end surface 82 of the endoscope 72, as shown in FIG. It can be observed in a fixed state that does not move due to suction. Note that an airtight seal member 85 such as an O-ring is provided between the endoscope 72 and the overtube 74 to maintain airtightness.

In this state, the surface can be observed in detail near the near point. Furthermore, the attention organization part 8
By irradiating the light to the center side by a prism 81 arranged so as to surround 3, a tomographic image can be obtained.

In other words, by switching the switching unit 76, a tomographic image in which the target tissue portion 83 is sliced from various directions around the center of the distal end of the endoscope can be obtained. Detailed diagnosis can be made.

When the diseased tissue is excised by mucosal resection (EMR) or the like, the treatment can be performed while confirming that the diseased tissue has been excised from the tomographic image.

[Supplementary Notes] An illumination unit that emits illumination light for illuminating a specific portion of the subject, an objective optical system that forms an image of the specific portion of the subject illuminated with the illumination light, and a solid-state imaging device that captures an image from the objective optical system. An elongated insertion portion that can be inserted into a subject, a light source that generates low interference light, and a light source that is inserted into the insertion portion and emits the low interference light to the subject from a side end surface on the distal end side of the insertion portion. In addition, a light guide means composed of one single mode fiber for detecting the reflected light reflected from the subject, and for scanning and emitting the light emitted from the single mode fiber from the distal end of the insertion portion in the circumferential direction. Driving means for rotating the single mode fiber,
Interference light extraction means for causing the reflected light from the subject detected by the single mode fiber to interfere with reference light generated from the light source and extracting an interference signal corresponding to the interfered interference light; Signal processing means for performing signal processing to construct a tomographic image in the depth direction of the subject,
In an optical tomographic imaging apparatus comprising a light emitted from the distal end of the insertion portion, the light irradiated to the subject is captured by the solid-state imaging device, and the direction of the light emitted from the distal end of the insertion portion is detected from the image, An optical tomographic imaging apparatus, comprising: a control circuit that controls a region or a direction in which the tomographic image is displayed based on the direction.

1 '. An illumination unit that emits illumination light for illuminating a specific portion of the subject, an objective optical system that forms an image of the specific portion of the subject illuminated with the illumination light, and a solid-state imaging device that captures an image from the objective optical system. An elongated insertion portion that can be inserted into a subject, a light source that generates low interference light, and a light source that is inserted into the insertion portion and emits the low interference light to the subject from a side end surface on the distal end side of the insertion portion. In addition, a light guide means composed of one single mode fiber for detecting the reflected light reflected from the subject, and for scanning and emitting the light emitted from the single mode fiber from the distal end of the insertion portion in the circumferential direction. A driving means for rotating the single mode fiber, and a reflected light from the subject detected by the single mode fiber interfering with a reference light generated from the light source to correspond to the interfering interference light. An optical tomographic imaging apparatus comprising: an interference light extraction unit that extracts an interference signal; and a signal processing unit that performs signal processing corresponding to the interference signal and constructs a tomographic image of the subject in a depth direction. The solid-state imaging device captures light emitted from the distal end of the insertion portion and irradiating the subject with the solid-state imaging device, and includes a control circuit that performs control to display a tomographic image of a portion corresponding to a region displayed as the image from the image. An optical tomographic imaging apparatus, characterized in that:

2. A display unit configured to specify a region of a specific portion of a subject to be imaged by the solid-state imaging device from the tomographic image and display a tomographic image of a portion selected by the region selecting unit. An optical tomographic imaging apparatus, characterized in that:

3. 2. The optical tomographic imaging apparatus according to claim 2, wherein the tomographic image selected by the designated area and the image of the subject obtained by the solid-state imaging device are simultaneously displayed.

4. 2. The optical tomographic image according to claim 1, wherein the means for detecting the emission direction comprises color extraction means for extracting the color of light emitted from the single mode fiber from an image signal generated by the solid-state imaging device. apparatus.

5. A laser light source for cauterizing a specific portion of the subject, an elongated insertion portion that can be inserted into the subject, a light source that generates low interference light, and a side end surface that is inserted into the insertion portion and that is on the distal end side of the insertion portion A light guide means comprising one single mode fiber for detecting the reflected light reflected from the subject, based on emitting the low interference light from the subject to the
A laser light combining means for guiding the laser light emitted from the laser light source to the light guiding means, and the single mode fiber for scanning and emitting the light emitted from the single mode fiber from the distal end of the insertion portion in the circumferential direction. Driving means for rotating the light source, and interference light for causing interference between reflected light from the subject detected by the single mode fiber and reference light generated from the light source to extract an interference signal corresponding to the interfered interference light In an optical tomographic imaging apparatus, comprising: an extracting unit, and a signal processing unit that performs signal processing corresponding to the interference signal and constructs a tomographic image in a depth direction of the subject. Region selecting means for extracting a part, and laser light controlling means for irradiating the specific part selected by the region selecting means with laser light from the laser light source; Optical tomography apparatus characterized by.

6. 5. The optical tomographic imaging apparatus according to claim 5, wherein the direction detecting means measures a time required for the emission direction to be directed from a predetermined reference point to the selected site.

7. 5. The optical tomographic imaging apparatus according to claim 5, wherein the laser beam combining means includes a dichroic mirror that transmits light in the wavelength band of the laser light and reflects light in the wavelength band of the low interference light.

[0080]

As described above, according to the present invention, illumination means for emitting illumination light for illuminating a specific portion of a subject;
An objective optical system that forms an image of a specific portion of the subject illuminated with the illumination light, a solid-state imaging device that captures an image from the objective optical system, an elongated insertion portion that can be inserted into the subject, and low interference A light source that emits light, and a light source that is inserted through the insertion portion, emits the low-interference light to the subject from a side end surface on the distal end side of the insertion portion, and detects reflected light reflected from the subject. Light guiding means comprising two single mode fibers;
Driving means for rotating the single mode fiber so as to scan and emit light emitted from the single mode fiber from the distal end of the insertion section in the circumferential direction; and reflected light from the subject detected by the single mode fiber. Interfering with the reference light generated from the light source, interference light extraction means for extracting an interference signal corresponding to the interfered interference light, performing signal processing corresponding to the interference signal, the depth direction of the subject Signal processing means for constructing a tomographic image of the optical imaging device, the light emitted from the distal end of the insertion portion and irradiating the subject is imaged by the solid-state imaging device, from the image, the image of the image Since a control circuit for controlling a portion corresponding to the region to be displayed as the tomographic image is provided, the tomographic image in the region corresponding to the region of the image captured by the solid-state imaging device is automatically generated. To can be displayed, thereby improving the operability.

[Brief description of the drawings]

FIG. 1 is an overall configuration diagram of an optical tomographic imaging apparatus according to a first embodiment of the present invention.

FIG. 2 is a diagram showing a configuration of an OCT processor.

FIG. 3 is a diagram showing an endoscope image.

FIG. 4 is an overall configuration diagram of an optical tomographic imaging apparatus according to a modification of the first embodiment.

FIG. 5 is a configuration diagram of an OCT processor according to a second embodiment of the present invention.

FIG. 6 is a diagram showing a configuration of a main part of the optical tomographic imaging apparatus.

FIG. 7 is a diagram showing a state in which the tip of the overtube is pressed against a living tissue.

FIG. 8 is a view corresponding to a section taken along line AA of FIG. 7;

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 ... Optical tomographic imaging device 2 ... Endoscope 3 ... Light guide 4 ... Light source device 5 ... CCU 6 ... Frame memory for normal images 7 ... Monitor 8 ... OCT processor 9 ... Optical scanning probe 11 ... Laser light source 12 ... OCT frame Memory 13 Color extraction circuit 14 Control circuit 16 Insertion section 17 Forceps channel 18 Lamp 21 Illumination lens 22 Subject 23 Objective lens 24 CCD 25 Infrared cut filter 26 Mosaic filter 31 SLD 32 , 34, 36 single-mode fiber 33 optical coupler 35 rotary joint 37 dichroic mirror 41 motor 42 gear 43 prism 45 mirror 46 actuator 48 control device 51 photodetector 53 demodulator 55 Computer

 ──────────────────────────────────────────────────続 き Continuing from the front page (72) Inventor Takeshi Ozawa 2-43-2 Hatagaya, Shibuya-ku, Tokyo Inside Olympus Optical Industrial Co., Ltd. (72) Inventor Hiroyuki Yamamiya 2-43-2 Hatagaya, Shibuya-ku, Tokyo Olympus Optical Co., Ltd. (72) Inventor Akihiro Horii 2-43-2 Hatagaya, Shibuya-ku, Tokyo Olympus Optical Co., Ltd. (72) Inventor Hitoshi Mizuno 2-43-2, Hatagaya, Shibuya-ku, Tokyo Olympus Optical Co., Ltd. (72) Inventor Jun Hiroya 2-43-2 Hatagaya, Shibuya-ku, Tokyo Tokyo Olympus Optical Co., Ltd. (72) Katsuichi Imaizumi 2-34-2 Hatagaya, Shibuya-ku, Tokyo No. Olympus Optical Co., Ltd. (72) Inventor Hidemichi Aoki 2-43-2 Hatagaya, Shibuya-ku, Tokyo Olympus Inside Gaku Kogyo Co., Ltd. (72) Inventor Masahiro Ohno 2-43-2 Hatagaya, Shibuya-ku, Tokyo Olympus Optical Co., Ltd. (72) Eiji Yasuda 2-43-2 Hatagaya, Shibuya-ku, Tokyo Olympus Inside the Optical Industry Co., Ltd. (72) Takefumi Uesugi, Inventor 2-43-2 Hatagaya, Shibuya-ku, Tokyo Inside Olympus Optical Corporation (72) Inventor Toshimasa Kawai 2-43-2, Hatagaya, Shibuya-ku, Tokyo Olympus Inside Optical Industry Co., Ltd. (72) Inventor Yoshinao Daiaki 2-43-2 Hatagaya, Shibuya-ku, Tokyo Olympus Optical Industry Co., Ltd. (72) Kenji Yoshino 2-43-2 Hatagaya, Shibuya-ku, Tokyo Olympus Optical Industry Co., Ltd.

Claims (1)

[Claims] An illumination unit for emitting illumination light for illuminating a specific portion of a subject, an objective optical system for forming an image of a specific portion of the subject illuminated with the illumination light, and capturing an image from the objective optical system A solid-state image pickup device, an elongated insertion portion that can be inserted into the subject, a light source that generates low-interference light, and a light source that is inserted into the insertion portion and that is inserted into the subject from a side end surface on the distal end side of the insertion portion. A light guide means comprising one single mode fiber for emitting the interference light and detecting the reflected light reflected from the subject; and transmitting the light emitted from the single mode fiber from the distal end of the insertion portion to the circumferential direction. In order to scan and emit the light, the driving means that makes the single mode fiber rotatable, and the reflected light from the subject detected by the single mode fiber interferes with the reference light generated from the light source, thereby causing interference. Interference light extraction means for extracting an interference signal corresponding to the interference light, and signal processing means for performing signal processing corresponding to the interference signal and constructing a tomographic image of the subject in a depth direction. In the tomographic imaging apparatus, light emitted from the distal end of the insertion portion and irradiating the subject is imaged by the solid-state imaging device, and the direction of light emitted from the distal end of the insertion portion is detected from the image. An optical tomographic imaging apparatus comprising a control circuit for controlling a region or a direction in which the tomographic image is displayed.